Sample analyzer and sample analysis method thereof

ABSTRACT

A sample analyzer with an optical detection device and a sample analysis method of the sample analyzer are disclosed. The optical detection device includes a fluid chamber, a light source and a light detector. The fluid chamber includes an illumination zone. An analyte flows through the illumination zone so as to form a sample stream. The light source illuminates the illumination zone to excite cell articles, reacted with a reagent, of the sample stream to emit a light signal. The light detector detects the fluorescent lights and transforms it into an electric signal. The light detector can include a silicon photomultiplier.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.17/136,871, filed Dec. 29, 2020, for SAMPLE ANALYZER AND SAMPLE ANALYSISMETHOD THEREOF, which is a continuation of U.S. patent application Ser.No. 16/848,701, filed Apr. 14, 2020, for SAMPLE ANALYZER AND SAMPLEANALYSIS METHOD THEREOF, which is a continuation of U.S. patentapplication Ser. No. 16/224,532, filed Dec. 18, 2018, for SAMPLEANALYZER AND SAMPLE ANALYSIS METHOD THEREOF, which is a continuation ofU.S. patent application Ser. No. 15/163,541, filed, May 24, 2016, forSAMPLE ANALYZER AND SAMPLE ANALYSIS METHOD THEREOF, which claims thebenefit of Chinese Patent Application No. 201610156013.7, filed Mar. 18,2016, each of which is incorporated herein by reference in its entirety.

TECHNICAL FIELD

The present disclosure relates to a sample analysis technology,especially relating to a sample analyzer and a sample analysis methodthereof.

BACKGROUND

A sample analyzer is used for analyzing cell articles of a biologicalanalyte, such as classification and amount count for cell articles. Thesample analyzer could be a blood analyzer or a flow cytometry.

The sample analyzer usually contains a sample collection device, areagent supplement device, a sample reaction device, an opticalmeasurement device and an analyte delivering device. The samplecollection device collects the sample from outside of the sampleanalyzer and delivers the sample into the sample analyzer. The reagentsupplement device draws reagents from outside of the sample analyzer andprovides reagents to the sample reaction device. The sample and reagentsare mixed and incubated in the sample reaction device to generate ananalyte. The analyte is delivered to the optical measurement device bythe analyte delivering device. The optical measurement device collectsdiffusion lights or fluorescent lights emitted from cell articles of theanalyte illuminated by a light source, transforms the diffusion lightsor fluorescent lights into electrical signals and implementsclassification and amount count for cell articles by analyzing theelectrical signals.

Please refers to FIG. 1, by detecting side diffusion lights andfluorescent lights at the same time, the sample analyzer could beimplemented for classification of white blood cells, such as 5 classclassifications of white blood cells, which classifies white blood cellsas lymphocytes, monocytes, neutrophils, eosinophils, and eosinophils.

The 5 class classifications of white blood cells could be conducted inone reaction test or in two reaction tests alternatively. For theclassifications with two reaction tests, white blood cells areclassified as 4 classes, which are lymphocytes, monocytes, eosinophils,and a cluster of neutrophils and eosinophils respectively in the firstreaction test. Neutrophils and eosinophils are classified and counted inthe second reaction test. The results from the first reaction test andthe second reaction test then be combined to achieve 5 classclassifications of white blood cells.

Immature granulocytes and reticulocytes of the analyte need to bedetected in clinical trials. Please refers to FIG. 1, immaturegranulocytes are granulocytes still developing, granulocytes in earlydevelopment stage contains more nuclein materials inside than matureone. With more nuclein materials, combination strength between afluorescent dye and nuclein materials would be more solid so thatstrength of fluorescent lights emits under laser induction would beraised accordingly. Therefore, by identifying the specificity offluorescent signals, the sample analyzer is able to detect immaturegranulocytes.

Please refers to FIG. 2, reticulocytes are red blood cells underimmature stage. Reticulocytes contains a small amount of RNA, and thestrength of fluorescent lights excited by a laser beam afterreticulocytes are dyed by a fluorescent dye are stronger thanfluorescent lights emitting from mature red blood cells. Therefore, byidentifying the specificity of fluorescent signals, the sample analyzeris able to detect reticulocytes. Under above, detection of fluorescentlight is very important for cells classification and amount count.

However, the excited fluorescent lights in the sample analyzer are quietweak. For example, the strength of the fluorescent lights usually staysat pW or nW orders of magnitude. Therefore, sensitivity of the opticalmeasurement device is demanded to satisfy very high standard toguarantee accuracy of fluorescent signals.

At present, a fluorescent light detector is usually implemented fromvacuum photomultiplier or avalanche photodiode in common. Generally,fluorescent lights detector is operated through cooperating with adetection circuit. A specific structure of the fluorescent lightdetector is shown in FIG. 3, the fluorescent light detector includes alight detector, a gain circuit module, a signal adjustment module and ananalog-digital (A/D) converter. The light detector includes aphotoelectric transducer and a current gain portion. The gain circuitmodule includes a current-voltage transferring and amplifying circuitand a voltage amplifier.

Vacuum photomultiplier is with advantages of high sensitivity, highlinear characteristic, high dynamic range and high signal/noise rate,and is able to detect fluorescent lights. However, vacuumphotomultiplier has large size and is very expensive, which aredisadvantages for system miniaturization and cost down of the sampleanalyzer.

Comparing with vacuum photomultiplier, avalanche photodiode is withadvantages of small size and low cost. On the other hand, current gainof an avalanche photodiode relative to vacuum photomultiplier is toosmall so as to cause the sensitivity of avalanche photodiode becomes lowcorrespondingly. For example, current gain of the vacuum photomultipliergenerally reaches 10⁵-10⁶, but current gain of avalanche photodiode isonly 10-10² on the other hand. Therefore, sensitivity of the avalanchephotodiode is hard to satisfy the requirements of fluorescent lightdetection. Therefore, an optical measurement device of a new sampleanalyzer with better performance/cost rate is demanded to satisfyclinical trials and solve above disadvantages.

SUMMARY

The application is for resolving at least one technical issues of thepresent technology. Therefore, a sample analyzer and a sample analysismethod is provided at the present application.

A sample analyzer in the embodiments of this application includes: asample collection device collecting a sample quantitatively, wherein thesample comprises cell particles; a reagent supplement device providing areagent, wherein the reagent is able to react with the cell particles; asample reaction device receiving the sample from the sample collectiondevice and the reagent from the reagent supplement device, wherein thereagent reacts with the cell particles to generate an analyte; ananalyte delivery device delivering the analyte for optical measurement;an optical measurement device measuring a light signal generated fromthe analyte to generate a light signal information, wherein the opticalmeasurement device comprises: a fluid chamber comprising an illuminationzone, wherein the analyte from the analyte delivery device flows throughthe illumination zone to form a sample stream; a light sourceilluminating the illumination zone to make the light signal to begenerated from the sample stream; and a light detector for detecting thelight signal and transforming the light signal into the light signalinformation, wherein the light detector comprises at least one siliconphotomultiplier.

In some embodiments, the sample analyzer includes a laser generator, theoutput power of the laser generator is between 1 to 20 mW. Preferably,the output power of the light source is selected from 5 to 15 mW.

In some embodiments, the sample analyzer includes a plurality of lightsensing units arranged in an array configuration, the number of thelight sensing units is larger or equal to 500 units. Preferably, thenumber of the light sensing units is larger or equal to 1000 units.Preferably, the number of the light sensing units is larger or equal to1280 units.

In some embodiments, a light sensing area of the silicon photomultiplieris smaller than a threshold value, a distortion of a pulse amplitude ofan electrical signal is triggered when the light sensing area of thesilicon photomultiplier exceeds the threshold value, the electricalsignal is generated according to an amount of dark pulse countoverlapping on single one of the cell particles.

In some embodiments, a light sensing area of the silicon photomultiplieris between 1-36 mm². Preferably, the light sensing area is a circle witha diameter between 1.1 mm to 6.8 mm. Preferably, the light sensing areais a circle with a diameter between 2 mm to 6 mm. Preferably, the lightsensing area is a square with a length between 1 mm to 6 mm. Preferably,the light sensing area is a square with a length of 3 mm.

In some embodiments, the optical measurement device includes an opticalpath, configured between the fluid chamber and the light detector, forconverging the light signal to form a facula on a light sensing area ofthe silicon photomultiplier, the facula is between 50% to 78% of thelight sensing area.

In some embodiments, the sample analyzer includes a controller forcontrolling a reverse bias voltage applied on the siliconphotomultiplier to keep an overvoltage between 0 to 5 volt, theovervoltage is a difference between the reverse bias voltage and abreakdown voltage of the silicon photomultiplier. Preferably, theovervoltage is under 3 volt. Preferably, the overvoltage is 1.5 volt.

In some embodiments, the controller adjusts the reverse bias voltageapplied on the silicon photomultiplier according to different operationmodes to control the overvoltage.

In some embodiments, the sample analyzer includes a temperature controldevice for controlling a temperature of the silicon photomultiplier at aconfiguration temperature. Preferably, the configuration temperature isselected between 20° C. to 40° C. Preferably, the configurationtemperature is selected between 25° C. to 35° C.

In some embodiments, the sample analyzer includes a temperaturecompensation device for adjusting a reverse bias voltage applied on thesilicon photomultiplier according to a temperature of the siliconphotomultiplier so as to keep an overvoltage constant. The temperaturecompensation device comprises a temperature sensor, a temperaturedetection circuit, an AD converter, a temperature compensation module, aDA converter, a voltage adjustment circuit and a regulation power supplywith an adjustable output, wherein the temperature sensor and thetemperature detection circuit detect the temperature of the siliconphotomultiplier and generate a temperature signal, the AD converterconverters the temperature signal into a digital signal, the temperaturecompensation module calculates a target value of the reverse biasvoltage of the silicon photomultiplier, the controller adjusts a circuitparameter of the voltage adjustment circuit by controlling the DAconverter to cause an output voltage of the adjustable regulation powersupply to reach the target value of the reverse bias voltage.

In some embodiments, a sample analysis method for a sample analyzer ofthe embodiments of this application includes: providing an analytecomprising cell particles treated with a reagent; providing an opticalmeasurement device comprising a fluid chamber, a light source and alight detector comprising at least one silicon photomultiplier; when theanalyte flows through the fluid chamber and forms a sample stream,illuminating the sample stream flowing through the fluid chamber by thelight source to generate a light signal, and transforming the lightsignal into light signal information after the light detector receivesthe light signal; and classifying the cell particles according to thelight signal information.

In some embodiments, the cell particles are at least selected from redblood cells, white blood cells and platelets.

In some embodiments, the light power of the light source is between 5 to15 mW.

In some embodiments, the silicon photomultiplier includes a plurality oflight sensing units arranged in an array configuration, an illuminationarea of each light sensing unit is smaller than an imaging area of asingle cell particle.

In some embodiments, the reverse bias voltage applied on the lightsensing units is larger than a breakdown voltage.

In some embodiments, a first reverse bias voltage is applied on thelight sensing units when the cell particles are white blood cells and asecond reverse bias voltage is applied on the light sensing unit whenthe cell particles are reticulocytes, the first reverse bias voltage issmaller than the second reverse bias voltage.

BRIEF DESCRIPTION OF THE DRAWINGS

For explaining embodiments of the present application or conventionaltechnology more clearly, figures used for explaining embodiments orconventional technology are shortly introduced below. Obviously, in thedrawings, similar drawings contain similar symbols for the same deviceor part, or for a part which has an analogous function and/or analogousstructure. It should be understood that these drawings describedifferent kinds of embodiments, but are not to be considered aslimitations of the scope.

FIG. 1 is a scatter diagram of white blood cell classification.

FIG. 2 is a scatter diagram of reticulocytes.

FIG. 3 is a functional module schematic of a fluorescent light detectioncircuit.

FIG. 4 is a functional module schematic of a sample analyzer for oneembodiment of the present invention.

FIG. 5 is an optical path schematic of the optical measurement device ofthe sample analyzer for one embodiment of the present invention.

FIG. 6 is a fluid chamber schematic of the optical measurement devicefor one embodiment of the present invention.

FIG. 7 is a structure schematic of a silicon photomultiplier for oneembodiment of the present invention.

FIG. 8 is an output signal characteristic diagram of single/multiplephotons detected by photosensitive units of the silicon photomultiplier.

FIG. 9 is a time-varying characteristic curve diagram of the outputsignal of a photosensitive unit.

FIG. 10 is an output signal characteristic diagram of lights withdifferent fluxes detected by the silicon photomultiplier. The leftfigure is the characteristic diagram for detecting lights with very weakfluxes (single photon level). The right figure is the characteristicdiagram for detecting lights with higher power.

FIG. 11 is a portion of the optical path schematic of the opticalmeasurement device for one embodiment of the present invention.

FIG. 12 is a voltage-varying characteristic curve diagram of thecrosstalk rate of the silicon photomultiplier.

FIG. 13 is a portion of functional module schematic of the sampleanalyzer for one embodiment of the present invention.

FIG. 14. is a portion of functional module schematic of a controller ofthe sample analyzer for one embodiment of the present invention.

FIG. 15. is a scatter diagram of white blood cells in a regular analyteanalyzed by the sample analyzer for one embodiment of the presentinvention.

FIG. 16 is a scatter diagram of white blood cells in an abnormal analyteanalyzed by the sample analyzer for one embodiment of the presentinvention.

FIG. 17 is a scatter diagram of reticulocytes analyzed by the sampleanalyzer for one embodiment of the present invention.

FIG. 18 is a scatter diagram of nucleated red cells of the sampleanalyzer for one embodiment of the present invention.

DETAILED DESCRIPTION

Specific details for fully understanding each of embodiments andimplemented by the skilled in the art are provided in bellowdescription. However, it should be understood for those skilled in theart that the present invention is able to be implemented without thespecific details as well. In some embodiments, conventional structuresand functions are omitted to avoid confusions in the descriptions of theembodiments.

Unless it is acquired clearly under context of the descriptions, theterms “comprise”, “include” should be defined as opening definition butnot limited or exhaustive definition.

According to the research for the sensitivity of the avalanchephotodiode when it operates as a fluorescent light detector, it is foundthat the sensitivity for detecting fluorescent lights of an avalanchephotodiode can be increased by several approaches listed below:

-   (1) controlling the area range of light sensor of the avalanche    photodiode, for instance, controlling the diameter or length of the    light sensor in the range between 0.1-2 mm.

However, by doing so, the specification requirement of an auxiliaryoptical path for the fluorescent light detector would be raised. Forexample, convergence lens should be implemented by special specificationaspheric lens under above condition.

In addition, the auxiliary optical path will become very sensitive andhard to be adjusted. Moreover, the specification requirement for thecontroller of the light detector would be raised as well. Such as, aproper low-pass filter, a proper high-pass filter and a proper basebandadjustor would need to be configured between the electrode capacitors ofthe avalanche photodiode, which cause the controller of the fluorescentlight detector to become more complicated.

Moreover, requirements for the control circuit of the light detectorwill become higher. For instance, a proper low pass filter, a high passfilter and a baseband adjustor are required to be configured accordingto the electrode capacitor of the avalanche photodiode. The controlcircuit of the fluorescent detector will become more complicatedcorrespondingly.

(2) Increasing Power of the Light Source of the Sample Analyzer

If the avalanche photodiode is implemented as the fluorescent lightdetector, for increasing sensitivity of the fluorescent light detector,a laser generator with 20 mW or a 25 mW power should be applied as thelight source. On the contrary, only 5 mW power laser generator is neededwhen the vacuum photomultiplier is implemented as the fluorescent lightdetector. A light source with higher power would significantly increasecost, for example, if power of the light source needs to be double, thecost of it is double as well accordingly.

(3) Increasing the Circuit Gain of the Avalanche Photodiode

For example, the circuit gain of the vacuum photomultiplier is generallybetween 10-100 KV/A, bur for generating output signals with the sameamplitude as the vacuum photomultiplier generating, the circuit gain ofthe vacuum photomultiplier needs to be increased to reach 1-50 MV/A. Itwould cause the noise rate of the fluorescent signals detected by theavalanche photodiode to be 50% higher than the noise rate detected bythe vacuum photomultiplier. For instance, the fluorescent light detectorimplemented by the vacuum photomultiplier is able to control the noiserate under 150 mVpp, thus, under the condition that the range of an A/Dconverter is 4 volt, noise is about to less than 4% of the detectionsignals. Instead, if the avalanche photodiode is implemented and thesensitivity of it is increased by the gain circuit, it would be hard tocontrol the noise of the fluorescent signals to be controlled under 300mVpp.

Increase of noise could cause negative effects on 5 classesclassification of white blood cell. More seriously, it would influencethe sensitivity for detecting abnormal cells and further affect theabilities for alarming when abnormal analyte appears. For example, inthe detection of immature granulocytes, although immature granulocytesdistribute on upon of the neutrophils on the direction of sidefluorescent light strength in the scatter diagram of the classificationof white blood cell, there is no significant interval betweenneutrophils group and immature granulocytes group. Since the neutrophilstake 50%-70% in all white blood cells, far greater than the percentageof immature granulocytes, it would be easy to misjudge neutrophils asimmature granulocytes when noise of the fluorescent signals is louderand vice versa. Louder the noise is, probability for negative orpositive misjudges is increased.

In addition, amounts of mature red blood cells are far more greater thanamounts of reticulocytes. (amounts of RBC for a regular adult isapproximately between 3.5-5.5×10¹²/L, and amounts of reticulocytes isonly between 0.02-0.2×10¹²/L, which is 0.5%-1.5% of RBC)

Therefore, boundaries between groups of reticulocytes and RBC would beblurred in the scatter diagram of reticulocytes detected by theavalanche photodiode. It would be easy to misjudge RBC as reticulocytesand vice versa when noise of the fluorescent signals is louder. Thesensitivity for detecting abnormal cells and the abilities for alarmingwhen abnormal analyte appears would go down correspondingly. In the meantime, the detection circuit is complicated and it's difficult to adjustthe optical path.

It is found in the research additionally, only above three ways areapplied at the same time will make the avalanche photodiode to satisfythe requirement of fluorescent light detector. Therefore, noise issuesare hard to overcome when the avalanche photodiode is operated as alight detector for fluorescent lights detection. The sensitivity fordetecting abnormal cells and the abilities for alarming when abnormalanalyte appears would go down correspondingly. In the mean time, thedetection circuit is complicated and it's difficult to adjust theoptical path.

Please refers to FIG. 4, a sample collection device 10, a reagentsupplement device 20, a sample reaction device 30, an analyte deliverydevice 40, an optical measurement device 50, a controller 60 and aprocessor 70 are disclosed.

The sample collection device 10 is implemented for quantitativelycollecting a sample and delivering the sample to the sample reactiondevice 30. In some embodiments, the sample collection device 10 includesa sampling needle, an injector and a clean swab for cleaning thesampling needle (not shown in FIGs). Obviously, the sample collectiondevice 10 is not limited to be implemented under above disclosures butis able to be configured according to requirements. For instance, insome other embodiments, the sample collection device 10 could furtherinclude an autoloader, a compartment, a sample rotary valve and ametering pump (not shown in FIGs).

The reagent supplement device 20 is implemented for collecting a rationreagent from a reagent tube or a reagent bin and delivering the rationreagent to the sample reaction device 30. In some embodiments, thereagent includes diluents, fluorescent dye and/or hemolytic agent. Thereagent is able to be configured according to the configuration ofmeasurement models. If only white blood cell classification model isconducted, the reagent should include diluents, a hemolytic agentcapable of lysing red blood cells and morphological processing whiteblood cells and a fluorescent dye only for white blood cell dying. Ifonly reticulocytes counting model is conducted, the reagent shouldinclude diluents, a hemolytic agent capable of conducting morphologicalprocessing for red blood cells and a fluorescent dye only forreticulocytes dying.

In some embodiments, the reagent supplement device 20 includes aninjector and necessary pipeline clean device. Obviously, the reagentsupplement device 20 is not limited to be implemented under abovedisclosures, but is able to be properly adjusted according to specificrequirement. Such as, in other embodiments, the reagent supplementdevice 20 could include a metering pump or a liquid storage pool forstoring multiple reagents.

The sample reaction device 30 is implemented for containing the sampleand the reagent to make the sample and the reagent to react forgenerating the analyte. In some embodiments, the sample reaction device30 could include a temperature control device and a blending device. Thetemperature control device is implemented for providing a propertemperature environment to the reaction between the sample and thereagent. 42° C. is selected in some embodiments. Obviously, thetemperature environment should be selected under requirements but notlimited in above discussed embodiments.

The blending device is implemented for sufficiently blending the sampleand the reagent. In some embodiments, the blending device, including anair pump and a control valve, could be implemented by generating bubblesto blend the sample and the reagent. It should be noted that theblending device could be implemented under other proper configuration inother embodiments but not limited to embodiments disclosed above. Forexample, the blending device, including an electrical mechanism, couldbe implemented by electric machinery for blending the sample and thereagent.

It should be understood that the entire sample reaction device 30 shouldbe configured under practical requirements in other requirements but notlimited to above embodiments. For instance, if reaction ability of thereagent is enough, the temperature control device and the blendingdevice of the sample reaction device 30 could be omitted. In addition,multiple sample reaction modules respectively selected as the samplereaction device 30 in different measurement models is acceptable. Forexample, the white blood cell classification and the reticulocytesclassification generally are conducted with different sample reactionmodules. That could increase detection performance firstly, and avoidcross pollutions among different measurement models secondly.

The analyte delivery device 40 is implemented for delivering the analyteinto the optical measurement device 50. Specifically, the analytedelivery device 40 delivers the analyte sufficiently reacted to theoptical measurement device 50. In some embodiments, the analyte deliverydevice 40 could include two injectors, a pipeline and a control valve.One of the injector is implemented for driving the analyte passingthrough the optical measurement device 50 via the pipeline.Specifically, one of the injector provides pressures to make the analytepassing through the optical measurement device 50 and the other injectoris implemented for driving diluents to form sheath fluid. The sheathfluid wraps up the analyte so as to form a sample stream passing throughthe optical measurement device 50.

The control valve could be configured on the pipeline for controllingon/off of the pipeline between different sample reaction devices to theoptical measurement device 50 so as to select a proper analyte into theoptical measurement device 50.

It should be understood that the analyte delivery device 40 should beconfigured under practical requirements in other requirements but notlimited to above embodiments. Specifically, the injector could bereplaced by an air source generating pressures or a liquid tank drivingby pressures.

The optical measurement device 50 is implemented for illuminating thesample stream, collecting diffusion lights and fluorescent lights ofcell articles when cell articles are illuminated and outputtingcorresponding electrical signals (diffusion light signal and fluorescentlights signals) of diffusion lights and fluorescent lights. In thisembodiment, the electrical signals respectively reflect strength of thelight signals (diffusion lights and fluorescent lights) so thatelectrical signals also can be defined as light signal information.

The optical measurement device. Please refers to FIG. 5, in someembodiments, the optical measurement device 50 includes a light source501, an irradiation lens group 502, a fluid chamber 503, a firstaperture 504, a first converging lens 505, a second aperture 506, afirst light detector 507, a second converging lens 508, a dichroicmirror 509, a third aperture 510, a second light detector 511, a fourthaperture 512, a longpass filter 513 and a third light detector 514.

In some embodiments, light source 501 could be implemented by a lasergenerator, such as a laser diode with 635 nm operation wavelength. Itshould be understood that the light source 501 should be configuredunder practical requirements in other requirements but not limited toabove embodiments.

In other word, flow cytometry are applied to the sample analyzer forcells classification and cells count. Of course, implementation of thefluid chamber 503 is not limited to above embodiments. Alternativescould also be applied in other embodiments for the requirements ofmeasurement.

In some embodiments, the irradiation lens group 502 is configured on thelight path between the light source 501 and the fluid chamber 503. Theirradiation lens group 502 is applied for converging lasers generated bythe light source 501 to form a proper facula illuminating theillumination zone 503 e. The facula focus on the cell articles 503 d inthe sample stream 503 c to generate diffusion lights and fluorescentlights.

Wherein, the diffusion lights includes forward low angle scatteringlights with 1-10 degrees angle compared to the optical axis and sidescattering lights basically vertical with the optical axis. The forwardlow angle scattering lights refers to the volume of the cell articles503 d. The side scattering lights refers to the complexity of insidestructure of the cell articles 503 d. The fluorescent lights includeside fluorescence basically vertical with the optical axis. The sidefluorescence refers to the content of DNA and RNA in the cell articles503 d.

Intensity of the forward low angle scattering lights is strongest.Intensity of the side scattering lights is less than it of the forwardlow angle scattering lights. Intensity of the side fluorescence is muchless than it of the forward low angles scattering lights and the sidescattering lights. In some embodiments, the irradiation lens group 502includes collimating lens and cylindrical lens.

In some embodiments, the irradiation lens group 502 includes collimatinglens and cylindrical lens. Of course, implementation of the irradiationlens group 502 is not limited to above embodiments. Alternatives couldalso be applied in other embodiments for the requirements ofmeasurement.

The first converging lens 505 is configured on the optical axis of thelight source 501 and located at the other side of the fluid chamber 503for collecting the forward low angle scattering lights. The firstaperture 504 is configured on the first converging lens 505 for blockingdirect lights. The first light detector 507 is configured on aconverging light path of the first converging lens 505, such as on aconverging spot, for collecting the forward low angle scattering lightsand transforming it as a corresponding electrical signal (forwardscattering light signal). The second aperture 506 is configured in thefront of the first light detector 507 for removing environment lights.

It is understood that an auxiliary light path of the first lightdetector 507 is constructed of the first aperture 504, the firstconverging lens 505 and the second aperture 506, which is applied forincreasing the detection performance and the signal noise rate of thefirst light detector 507.

For certain, implementation of the auxiliary light path of the firstlight detector 507 is not limited to above embodiments, alternativescould also be applied in other embodiments for the requirements ofmeasurement.

The second converging lens 508 is configured on a light path basicallyvertical with the fluid chamber 503 and the light source 501 forcollecting the side scattering lights and the side fluorescent lights.The dichroic mirror 509 is configured on the converging light path ofthe second converging lens 508 for separating the side scattering lightsand the side fluorescent lights. The second light detector 511 isconfigured on the light path of the side scattering lights of thedichroic mirror 509, such as located on the converging spot, forcollecting side scattering lights and transforming it as a correspondingelectrical signal (side scattering light signal). The third aperture 510is configured in the front of the second light detector 511 for removingthe environment lights. The third light detector 514 is configured onthe light path of the side fluorescent lights of the dichroic mirror509, such as located on the converging spot, for collecting the sidefluorescent lights and transforming it as a corresponding electricalsignal (fluorescent light signal or side fluorescent light signal). Thelong pass filter 513 and the fourth aperture 512 are both configured inthe front of the third light detector 514 in sequence for removing straylights in the light path and environment stray lights other thanfluorescent light wavelength.

It is understood that an auxiliary light path of the second lightdetector 511 and the third light detector 514 is constructed of thesecond converging lens 508, the dichroic mirror 509, the third aperture510, the long pass filter 513 and the fourth aperture 512. The auxiliarylight path is applied for increasing the detection performance and thesignal noise rate.

For certain, implementation of the auxiliary light path of the secondlight detector 511 and the third light detector 514 is not limited toabove embodiments, alternatives could also be applied in otherembodiments for the requirements of measurement. It should be noted thatin some other embodiments, some elements of the optical detection device50 could be omitted, such as the second aperture 506.

For some embodiments, in the consideration of the condition that forwardscattering lights and side scattering lights are relative stronger,sensitivity of the PIN photodiode is enough to satisfy with therequirements for measuring. Therefore, the first light detector 507 andthe second light detector 511 are able to be implemented by applying lowcost PIN photodiode so as to cut down the cost of the sample analyzer.

Since the intensity of the side fluorescent lights is much less thanthat of the forward scattering lights and the side scattering lights,disadvantages of large volume and high cost are raised if vacuumphotomultiplier is implemented. On the other hand, although cost is cutdown, the disadvantage of lack of enough sensitivity is also raised whenthe avalanche photodiode is implemented.

Please refers to FIG. 7, the third detector 514 includes a planar arrayconsisting of multiple light sensors. Each light sensor includes a microelement of light sensing diode 514 a and a quench resistor 514 bconnecting in series with each other. The size of the light sensor isbetween several microns to hundreds of micron. The amount of the lightsensors should be between hundreds to ten-thousands. The resistance ofthe quench resistor 514 b is normally between several hundred Ohms tomega-ohms.

The silicon photomultiplier is with advantages of small volume, highsensitivity (gain is high to reach 10⁶, which is close to the gain ofvacuum photomultiplier), low operation voltage (generally dozens ofvolts), low cost (less than 1/10 of vacuum photomultiplier, almost equalto avalanche photodiode) and low sensitivity for magnetic field.

Therefore, silicon photomultiplier is applied to implement as the thirdlight detector 514 so as to make the optical detection device 50 and thesample analyzer having advantages of high sensitivity, high signal noiserate, small volume and low cost.

Please refers to FIG. 8 as well, each of light sensor operates under theGeiger-mode. For example, when a reverse bias voltage over the breakdownvoltage of the micro unit of the light sensing diode 514 a is applied onthe light sensor, the current passing through the light sensing diode514 a would increase significantly. However, since there is quenchresistors 514 b in this light sensor, when voltage drop generated fromthe quench resistor grows, it causes the reverse bias voltage on thelight sensing diode 514 a to become smaller than the breakdown voltage.Therefore, current amplifying effect ends and the outputting mode of thelight sensing diode 514 a turns back to its initial state, which is amode for outputting current impulses with fixed range. In this process,current gain could reach 10⁵-10⁶, so that the light sensing diode isworkable to be applied for single photon detection.

Light detector unit is operated as a photon trigger. Output signal(current) of it only has two state “0” or “1”. In its state “1”,amplitude of the output signal is not relative with the number ofemitting photons but fixed. It means no matter how much photon emit tothe light sensor unit in the meantime, the output signal is basicallyfixed with a constant amplitude the same as only one photon emits to thelight sensor unit.

Please refers to FIG. 9, another feature of output signal of the lightsensor unit is shown. After photons are detected, the output signalwould reach the fixed maximum value in very short time (usually duringfew nanoseconds) then starts to decay and returns to zero. Decaying timeof above is defined as recovery time, as well as dead zone time, usuallywith hundreds nanoseconds. In this recovery time, even next photonreaches to the light sensor unit, there is no any signal outputted fromthe light sensor at all. Only after the recovery time, next detectionperiod for detecting photons could be conducted.

Detection methods for detecting fluorescent lights among siliconphotomultiplier, light sensor unit and avalanche photodiode are totallydifferent. The avalanche photodiode must operate on linear mode totransform different light strengths into electrical signals withdifferent strengths when it is applied to detect fluorescent lights. Inthe other word, reverse bias voltage should be configured underbreakdown voltage to detect fluorescent lights so that the amplitude ofthe output signal is proportional to the strength of input light.However, under linear mode, the maximum current gain is generallybetween dozens or hundreds times. On the contrary, when the siliconphotomultiplier disclosed in this application is applied to detectfluorescent lights, each of the light sensor unit works at theGeiger-mode, in which the amplitude of the output signal for a singlelight sensor unit is basically a fixed value, would not increasecorresponding to the increase of the strength of input lights. Theadvantage of above is that the maximum current gain under theGeiger-mode can reach 10⁵-10⁶ so that the sensitivity of the siliconphotomultiplier can stand on a very high level. The siliconphotomultiplier of the present application consists of light sensorunits array, in which the area of single light sensor unit is much lessthan the area of fluorescent facula. In the other word, the area ofsingle light sensor unit is less than the area of imaging for a singlecell article. In ideal condition, the single light sensor would receivethe illumination of single photon to generate an electrical signal for asingle photon. As shown in FIG. 10, since large numbers and high densityof light sensor units are integrated as the silicon photomultiplier, theoutput of the silicon photomultiplier in an unit time is the output sumof all of the light sensors. Therefore, the silicon photomultiplierdisclosed in this application is able to transform lights with differentstrengths into electrical signals with different strengths and with veryhigh sensitivity as well.

The controller Please refers to FIG. 4, FIG. 13 and FIG. 14 at the sametime, the controller 60 includes a measurement circuit 60 a and acontrol circuit 60 b. In some embodiments, the measurement circuit 60 aincludes a current-voltage transformation amplifier 601 c, a high-passfilter 602 c, an anti-aliasing filter 603 c and AD converter 604 c. Thecurrent-voltage transformation amplifier 601 c could configure thecircuit gain for the third light detector 514 (the siliconphotomultiplier).

Besides above current-voltage transformation amplifier 601 c, ahigh-pass filter 602 c, an anti-aliasing filter 603 c and AD converter604 c, the measurement circuit 60 a further includes current-voltagetransformation amplifiers 601 a and 601 b, high-pass filters 602 a and602 b, anti-aliasing filters 603 a and 603 b and AD converter 604 a and604 b.

Electrical signals outputted from the first light detector 507, thesecond light detector 511 and the third light detector 514 pass throughthe current-voltage transformation amplifiers 601 a, 601 b and 601 c toconduct current/voltage transformation and respectively transmit intothe AD converters 604 a, 604 b and 604 c after signal processing totransform the electrical signals into digital signals in favor of theprocess of the processor 70.

It means current-voltage transformation amplifiers 601 a, 601 b and 601c are respectively applied for transforming current signals outputtedfrom the first light detector 507, the second light detector 511 and thethird light detector 514 into voltage signals.

Regarding to forward scattering light signals, a signal processingcircuit usually includes the high-pass filter 602 a with lower cut-offfrequency. It is useful for filtering direct light signals andeliminating baseline fluctuation in low frequency. However, differentfrom using avalanche photodiode for detecting fluorescent lights andside scattering lights, the sample analyzer of this application usingsilicon photomultiplier as the light detector. For detecting sidescattering light signals and fluorescent light signals, the high-passfilter 602 b and 602 c are not necessary since the baseline fluctuationof the high-pass filter 602 b and 602 c can be omitted. Therefore, thehigh-pass filter 602 b and 602 c can be omitted in some embodiments.

Base on general design principle, before the electrical signals aretransmitted into the AD converter 604 a, 604 b and 604 c, preferably,electrical signals should be processed by anti-aliasing filters 603 a,603 b and 603 c at first. Purpose of above preference is to prevent thehigh frequency portion of signals to be converted as part of lowfrequency interference overlapping with useful signals in the samplingprocess.

In addition, in some other embodiments, the measurement circuit 60 a isconfigured after the current-voltage transformation amplifiers 601 a,601 b and 601 c, including a voltage amplifier with adjustable gain, forimplementing the purpose of calibrating scatter diagram position.

In some other embodiments, calibration of the scatter diagram positionis implemented by configuring a digital amplifier in the processor 70.The control circuit 60 b is applied for controlling and driving relativeportions about electromechanical elements, fluid path and temperaturecontroller of the sample collection device 10, the reagent supplementdevice 20, the sample reaction device 30 and the analyte delivery device40 to finish the detection operation. The processor 70 is applied forprocessing the digital signals outputted from AD converter 604 a, 604 band 604 c to get a test result.

It should be understood by skilled in the art that the control circuit60 b and the processor 70 could be integrated as a single controller,which could be implemented by a microcontroller unit. Above individualdescriptions of this application for the control circuit 60 b and theprocessor 70 are only disclosed for clear explanation, but notlimitations of this application.

Please refers to FIG. 15, above disclosed sample analyzer could classifylymphocytes, monocytes, eosinophils, and neutrophils to achieving 4classes of white blood cells. After disposing the sample by otherreagent and classifying and amounting eosinophils through intensityinformation of forward scattering lights and intensity information ofside scattering lights, the result of the 4 classes for white bloodcells is combined with the result of eosinophils to realize a result of5 classes for white blood cells.

Moreover, it is found in the research and development stage that, underideal circumstance, if the number of incident photons is less than thenumber of light sensor units of the silicon photomultiplier and isdistributed on the illumination zone on average, the current impulseamplitude for the output signal of the silicon photomultiplier would belinearly relative with the instant power of incident lights well. But,if the number of effect incident photons is greater than the number oflight sensor units of the silicon photomultiplier or incident photonsover concentrate on a few of light sensor units of the siliconphotomultiplier, too many photons will emit on the same light sensorunit at the same time, the relation between the current impulseamplitude for the output signal of the silicon photomultiplier and theinstant power of incident lights would not remain linearity.

For the sample analyzer, when linearity of the fluorescent signal is notenough, gaps among different cell clusters will get narrower in thescatter diagram. For example, in the white blood cell classificationscatter diagram, fluorescent signals with bad linearity could cause lackof distinction between monocytes and neutrophils so as to influence themeasurement result and warning sensitivity of the sample analyzer in theend. In the meantime, lack of linearity would cause the dynamic range ofmeasurement to become insufficient as well.

For resolving issues relating to lack of linearity or dynamic range, byresearch, above issues could be resolved from two approaches: increasingthe number of light sensor units of the silicon photomultiplier andreducing the number of photons emitting on single light sensor unit atthe same time, which can also be defined as reducing luminous power onsingle unit area. Above ways are disclosed hereafter respectively:

Approach one: increasing the number of light sensor units of the siliconphotomultiplier. In one embodiment of this application, the number ofthe light sensor units on the light detector is optimized.

As described above, the reason of lack of linearity could be that toomany photons emit on the same light sensor unit at the same time so asto cause the output signal of the light sensor unit in this circumstanceequals to the output signal outputted when only a photon emit on lightsensor unit. For resolving that, by increasing the number of lightsensor units in single unit area, the probability that multiple photonsfalls on the same light sensor unit should reduce. Calculation for thenumber of the light sensor units is described below:

Relation between the power of the incident light and the number ofemitting photons is listed below:

Pt=NE=Nhc/λ

Wherein, P is the power of incident light, t is time, N is the number ofincident photons in time period t, E is the energy of single photon,h=6.63×10⁻³⁴, which is Planck constant, c=3×10⁸ m/s, which is lightspeed, λ is wavelength.

In some embodiments, the laser emitted from the light source 501 is with635 nm wavelength. The wavelength of exciting fluorescent lights λ=670nm. Therefore, E=2.97×10⁻¹⁹ J.

The width of fluorescent light pulse generated is 1 us when the cellarticle 503 d passes through the illumination zone 503 e and isilluminated. In this process, maximum number of incident photonsinstantly appears at the period t=100 ns of the top of the fluorescentlight.

In some embodiments, the power of the light power is 5 mW, maximuminstant power generated from the cell article 503 d is about P=30 nW,but the photon detection efficiency of the silicon photomultiplier isonly about 10% in the wavelength of 670 nm. It means only about 3 nW for30 nW of maximum instant optical power is sensed effectively. The numberof photons correspondingly sensed in above description is aboutN=Pt/E=1000.

Therefore, if the fluorescent facula is controlled to completely locateon the light sensing area of the silicon photomultiplier and each photonindividually hits on different light sensing area of each light sensorunits with no overlap, at least 1000 light sensing units are required.Moreover, since the sensing area of the silicon photomultiplier isusually formed as square but the fluorescent facula is usually circularor oval, the effectively utilizing area of the silicon photomultiplierwould be 78% at most so that 1280 light sensing units are required atleast.

However, design for the number of light sensor units of the siliconphotomultiplier should not be limited to above disclosed embodiments. Itshould be understood that specific number of the light sensor unitsshould be determined under practical requirements. For example, itshould be determined according to the intensity of the fluorescentgenerated. If the intensity of the fluorescent lights is weaker, thenumber of the light sensor units needed is reduced. Otherwise, thenumber of the light sensor units is increased. For some certainembodiments, better linearity and dynamic range could be acquired if thenumber of the light sensor units is over 500.

In the embodiments of this application, the area of the light sensingunit is optimized. The area of the light sensing unit could properly beincreased. Under above, it is no need to control the diameter or lengthof the light sensing unit to be maintained between 0.1-2 mm ranges.

In the condition that light sensing area of the silicon photomultiplieris under 1 mm², accuracy requirements for machining and assembling ofauxiliary light path of the second light detector 511 and the thirdlight detector 514 would become higher to make sure the fluorescentfacula precisely falls within the light sensing area of the siliconphotomultiplier. In the meantime, the light path would become verysensitive so as to make optical adjustment become harder, which wouldincrease cost.

On the other hand, light sensing area of the silicon photomultipliershould be preferably less than a light sensing threshold area of thesilicon photomultiplier. The light sensing threshold area is defined asa threshold area triggering a distortion of pulse amplitude of thefluorescent signal, the fluorescent signal is generated according to theamount of a dark pulse counts overlapping on single cell particle. Inthis embodiment, the light sensing threshold area is preferably lessthan 36 mm², because when the light sensing area of the siliconphotomultiplier is more than 36 mm², the amount of dark pulse count ofthe silicon photomultiplier will increase significantly so as to causethe noise of the silicon photomultiplier raises accordingly.

In this embodiment, dark count is defined as the number of current pulseper second outputted from the silicon photomultiplier without lightinput. Dark count is caused by avalanche effect came from thermions ofthe light sensing diode 514 a. Therefore, amplitude of current pulse fordark count is equal to amplitude of current pulse for a single photon.Dark count rate usually stays at 30 KCPS/mm² (KCPS is abbreviation forthousand units per second). Larger the area of the siliconphotomultiplier is, more dark count is generated accordingly. In theworst condition, dark count pulse will overlaps on the fluorescentsignal pulse generated from the cell particle 503 d so as to causedistortion of pulse amplitude. Less weak the fluorescent is, the effectof distortion is become worse. For the sample analyzer, width of thefluorescent light of the cell particle 503 d is generally 1 us and theperiod of the fluorescent light of the cell particle 503 d is at least10 us. For limiting the effect of dark count, dark count pulse should becontrolled to appear as less as possible in 0.3 us area on the top offluorescent signal pulse, which requests the dark count rate should becontrolled under 3.3 MCPS (MCPS is abbreviation for million counts persecond). That means, light sensing area of the silicon photomultipliershould be less than 36 mm².

Therefore, reasonable area of light sensing area of the siliconphotomultiplier is between 1-36 mm², shape of the light sensing areacould be circular with diameter between 1.1-6.8 mm, such as circle withdiameter between 2-6 mm. It could be a square with length between 1-6 mmor other shape with the same area, such as rectangle as well. In someembodiments, light sensing area of the silicon photomultiplier is shapedas a square with 3 mm length, which of area is 9 mm².

In one embodiment of this application, size for a single light sensingunit of the light detector is optimized. Size reduction of the singlelight sensing unit is helpful for increasing number of light sensingunits in the silicon photomultiplier. Above number increase reduces thepossibility of multiple photons reception in one single photon at thesame time.

When light sensing area of the silicon photomultiplier is between 1-36mm² and the number of the light sensing units is at least 1280, lengthof each light sensing unit should be less than 167 um as the siliconphotomultiplier is shaped as square.

Concerning the recovery time for the light sensing unit after occurrenceof the avalanche effect is positive correlative to capacitance value ofthe light sensing unit, it is understood that more the size of the lightsensing unit is, equivalent capacitance growths correspondingly so as toextend the recovery time. Since the light sensing unit is with nofunction for detecting next photon during the recovery time and the sidefluorescence generated by the sample analyzer is a multiple photonssignal with sustained duration about 1 us, accordingly, number ofphotons unable to be detected by the light sensing unit would increasein quantity when the recovery time is getting longer so that linearitybetween photon numbers and outputting current is influenced relatively.

When the size of the light sensing unit is more than 50 um and therecovery time increases to be more than 500 ns, it means only twophotons could be detected by each light sensing unit during the durationof fluorescence generated by a cell particle, which could influence thedetection result significantly. Therefore, a proper size for the lightsensing unit should be defined as 50 um or under 50 um, so as to controlthe recovery time below 300 ns.

However, size of the light sensing unit also relates to the current gainof the silicon photomultiplier. When the size of the light sensing unitis under 10 um, current gain would reduce to be fewer than 10⁵accordingly. Therefore, the circuit gain of the silicon photomultipliershould be improved, which would cause noise increase in the mean time.That is not propitious for the silicon photomultiplier to get closer orbetter noise characteristic comparing with vacuum photomultiplier.

Therefore, proper size of the light sensing unit should be controlledbetween 10 um to 50 um as accurate as possible. In some embodiments,size of the light sensing unit is about 35 um.

In conclusion under above, light sensing area of the siliconphotomultiplier could be controlled between 1-36 mm², size of the lightsensing unit could be controlled between 10 um-50 um and the number ofthe light sensing unit could be controlled at 1280 units or above.

Approach two: reducing incident photons in one single light sensing unitat the same time. Or rather, reducing light power in unit area. Inanother embodiment of this application, light source power in theoptical detection device is conducted optimization.

Because laser emitted from the light source 501 generates forwarddiffusion light, side diffusion light and fluorescent light at the sametime when the laser illuminates on the cell particle 503 d, max power ofthe side diffusion light could probably reach 20 uW. As disclosed above,PIN type photodiode is implemented as the second light detector 511 todetect side diffusion light for reducing cost of the sample analyzer andthe sensitivity of PIN type photodiode is about 0.4 A/W. Therefore, forrequiring side diffusion light signal with proper amplitude, detectioncircuit gain of the PIN type photodiode is generally configured to beover 700 KV/A. In addition, circuit bandwidth should be remained over500 KHz so that noise of PIN type photodiode could probably over 30 mVppunder this condition. The less the laser power is, the more noise of thedetection circuit of PIN type photodiode become, which means thesignal/noise rate gets worse accordingly. Worse signal/noise rate wouldinfluence the scatter diagram of white blood cells classification or thescatter diagram of reticulocytes significantly, so as to influenceclassification or counting of cells in the end. Therefore, in someembodiments, power of the light source 501 is preferably over 5 mW. Ofcourse, in some other embodiments that the avalanche photodiode isimplemented for detecting side diffusion light, power of laser could becontrolled under 1 mW, but cost would increase accordingly for thisimplementation.

Therefore, light source over 1 mW could be applied as the light sourceof this application. In the comprehensive consideration of performanceand cost, light source power limited under 20 mW is more preferable.Preferably, light source power between 5-15 mW is selected. Moreover, aproper light source power of above should be able operate between 5-15mW and to be adjusted dynamically according to requirements.

In another embodiment of this application, optimization for therelationship between fluorescent facula and light sensing area of theoptical detection device is conducted. If light power of the lightsource is remained steady, the number of incident photons illuminatingon a single light sensing unit at the same time could be reduced byenlarging facula area of the side fluorescent light. On the other hand,for making facula of the side fluorescent light to cover the lightsensing area of the silicon photomultiplier as large as possible, lightsensing area of the silicon photomultiplier is enlarged correspondinglyso as to achieve the same effect of increasing the linearity of the sidefluorescent light signal.

Please refer to FIG. 11, the side fluorescent light from the fluidchamber 503 passes through the second converging lens 508 to be focused,then the focused side fluorescent light projects on the light sensingarea of the third light detector 514. The distance between the thirdlight detector 514 and the forth aperture 512 is adjusted according tothe size of the light sensing area of the third light detector 514 tomake sure that the facula of the side fluorescent light is small thenthe light sensing area but occupies the whole light sensing area aslarge as possible. Shape of the facula of the side fluorescent light isgenerally circle or ellipse. If the light sensing area is square, faculaarea of the side fluorescent light should be between 50%-78% of thelight sensing area.

On the other hand, when the optical detection device is controlled todetect fluorescent lights, noise issues would be brought out sincesignal enlargement is conducted. Researches show that noise issue of thesilicon photomultiplier is mainly from light crosstalk between darkcount and light sensing unit. As disclosed above, the noise issue ofdark count could be controlled properly when the light sensing area ofthe silicon photomultiplier is less than 36 mm². In some embodiments,light sensing area of the silicon photomultiplier is about 9 mm², anddark count rate could be controlled under 1 MCPS on the whole. Underabove condition, influence of signal pulse could be ignored basically.Therefore, by selecting proper light sensing area, noise issue caused bydark count could be reduced effectively.

Light crosstalk between different light sensing units could be optimizedfrom several approaches disclosed below. For instance, in anotherembodiment of this application, overvoltage configuration in the opticaldetection device is optimized for reducing noise issue.

Light crosstalk between different light sensing units happens whenphotons are released from a light sensing unit at avalanche state andcoupled into another light sensing unit as incident photons, which wouldcause avalanche effect in the latter light sensing unit and generate acurrent pulse accordingly. At present, crosstalk rate of the siliconphotomultiplier generally stays between 5%-10%. In another word, underthe condition of ignoring dark count influence, when 100 photons emitinto the silicon photomultiplier, current pulses generated accordinglymay possibly equal to the ideal current pulse generated from 105-110incident photons, or rather, noise amplitude generated by lightcrosstalk between different light sensing units is about 5%-10% of anideal signal. Above disclosed noise level of the silicon photomultiplieris worse than vacuum photomultiplier.

However, crosstalk rate of the silicon photomultiplier is highlyrelating to overvoltage applied on the silicon photomultiplier. Whencrosstalk rate increases, crosstalk rate increases correspondingly. Theovervoltage is defined as the difference between reverse bias voltageapplied on the silicon photomultiplier and the breakdown voltage of thesilicon photomultiplier.

Please refer to FIG. 12, it is found after experiment that crosstalkcould be controlled to be less than 1% when the overvoltage is reducedto 1.5V. In this way, the light crosstalk noise of the siliconphotomultiplier is superior to the light crosstalk noise of vacuumphotomultiplier.

In some embodiments, the reverse bias voltage of the siliconphotomultiplier is configured to be slightly larger than the breakdownvoltage of the silicon photomultiplier. The overvoltage is definedaround 1.5V. However, it should be noted that it is suitable at all toconfigure the overvoltage below 3V for acquiring a noise level withcharacteristic matching with the noise level of vacuum photomultiplier.For certain, in some other embodiments, in the condition that the noiselevel is acceptable, to configure the overvoltage below 5V should beallowable as well.

Meanwhile, in the sample analyzer of this application, noise issue isreduced through temperature control for the silicon photomultiplier.Silicon photomultiplier is a kind of temperature sensitive element. itscurrent gain is varied with temperature obviously. That is because thebreakdown voltage of the light sensing diode micro unit is raised withclimbing temperature accordingly. If the reverse bias voltage of thesilicon photomultiplier stands steady, overvoltage is declined withclimbing temperature on the contrary. In the mean time, current gain ispositive relating with overvoltage. Therefore, climbing temperaturewould cause decline of gain. In conclusion, if current gain cannot bemaintained constantly, detection result would be influenced in thedetection process of the sample analyzer.

In one embodiment, temperature control for the silicon photomultiplieris implemented by applying constant temperature control so as to makethe silicon photomultiplier working on a configuration temperature. Theconfiguration temperature is a temperature selected between 20° C. to40° C., preferably between 20° C. to 40° C. A temperature control deviceis required for above temperature control solution, including a sealedtemperature control chamber, a heater/cooler and a driving controllerrelating. Of course, additional elements disclosed above would increasethe cost and volume of the sample analyzer.

Moreover, it should be understood that reduction of the temperature ofthe silicon photomultiplier helps to reduce the dark count of thesilicon photomultiplier, but quality requirements for the cooler and thetemperature control chamber would be stricter correspondingly, whichwould further raise the cost.

In another embodiment, noise issue is decreased through temperaturecompensation for the silicon photomultiplier. For example, temperaturecompensation could be applied for the reverse bias voltage, which meansto adjust the reverse bias voltage of the silicon photomultiplier inreal time according to current temperature of the siliconphotomultiplier so as to remain the reverse temperature constantly.Above temperature compensation solution is implemented only by adjustingthe reverse bias voltage of the silicon photomultiplier. It basicallyincreases no cost and volume of the sample analyzer comparing with thetemperature control solution. Therefore, in some embodiments,temperature compensation is applied to keep the stability of the currentgain of the silicon photomultiplier.

Please refer to FIG. 13, the sample analyzer of the present embodimentincludes a temperature compensation device. The temperature compensationdevice includes a temperature sensor 701, a temperature detectioncircuit 702, an AD converter 703, a temperature compensation module 704integrated in the controller 60, a DA converter 705, a voltageadjustment circuit 706 and a regulated power supply 707 with anadjustable output.

The temperature sensor 701 and the temperature detection circuit 702 areused for detecting the environment temperature of the third lightdetector 514 and generating a temperature signal. The temperature signalis converted as a digital signal by the AD converter 703. The digitalsignal is transmitted to the controller 60, by which a target value ofthe reverse bias voltage for the third light detector 514 is calculatedby the temperature compensation module 704.

In some embodiments, operation of the temperature compensation modulefollows below equation:

V _(bias) −V ₀ +k(T−T ₀)+V _(OV)

Wherein, V_(bias) is defined as the target value of the reverse biasvoltage applied on the silicon photomultiplier. V₀ is defined as thebreakdown voltage of the silicon photomultiplier at temperature k,usually is a constant. T is the current temperature, V_(OV) is theovervoltage. The breakdown voltage of the light sensing diode micro unit514 a is changed from V₀ to V₀+k(T−T₀). Therefore, only if the reversebias voltage on the silicon photomultiplier is adjusted to the targetV_(bias), the overvoltage would remain stable correspondingly so as tokeep the current gain steady. Both V₀ and k could be confirmed on themanual of the silicon photomultiplier. V_(OV) could be configuredaccording to requirements, such as 1.5 V in some embodiments.

After the target value of the reverse bias voltage is confirmed, thecontroller 60 adjusts the circuit parameters of the voltage adjustmentcircuit 706 (for instance, it is a feedback voltage in someembodiments.) by controlling the DA converter 705, so as to make theoutput voltage of the adjustable regulated power supply 707 (rather say,the reverse bias voltage) to reach the target value of the reverse biasvoltage.

By using the above sample analyzer to detect blood samples, white bloodcell classification could be realized. Moreover, abnormal sample couldbe detected under above as well, which is shown in FIG. 16. In someembodiment, by using the nuclear red blood cell scatter diagram withnuclear red blood cells count, basophile granulocytes could be detected.

In the sample analyzer of another embodiment of this application,multiple detection modules could be realized. It means, for detectingdifferent kinds of cell particle, different kind of samples are acquiredby applying different regents to react with different samples, ordifferent optical detection parameters are applied for samplesdetection. In particular, because white blood cell and reticulocytesgenerate fluorescent signals with different strengths respectively afterdyed, higher sensitivity would be acquired through applying differentoptical detection parameters to acquire stable and reliable result.Therefore, above disclosed temperature control device or temperaturecompensation device are able to keep the current gain of the sampleanalyzer steady in the detection process under the same detectionmodule. In the meantime, the controller 60 is able to configuredifferent overvoltage according to different detection modules to getdifferent current gains so as to acquire different signal amplifyingeffects. For example, fluorescent lights generated under reticulocytesdetection mode is often weaker than those under the detection module forwhite blood cell classification. Correspondingly, the controller 60would adjust overvoltage to increase the current gain underreticulocytes detection module.

However, adjustable range for the current gain of the siliconphotomultiplier is generally at five times, but strength differences offluorescent lights under different detection modules could be over than10 times. Therefore, for implementing the reticulocytes detection moduleand the white blood classification on the same sample analyzer,adjustable range for the gain of the silicon photomultiplier is stillnot satisfied.

For this, in some embodiments, it is acceptable for applying bothtemperature compensation device and detection circuit to adjust currentgain and circuit gain at the same time to satisfy detection requirementsunder different detection modules.

For instance, in some embodiments, the current/voltage convertingamplifier 601 c is at least able to configure two circuit gains. Eachkind of the circuit gains is corresponding to different measurementmodules respectively. When the detection modules of the sample analyzeris changed, the current/voltage converting the amplifier 601 c switchesbetween different circuit gains by adjusting current gains through thetemperature compensation device.

Of course, in some embodiments, another approach is to keep the currentgains steady for controlling the distortion rate, but only change thegain of amplifier to fit the requirements under different detectionmodules. In addition, in above embodiments, since the circuit gain isfar smaller than the current gain, the circuit noise could be ignored soas to control signal/noise rate.

In some embodiments, it is also workable to change the power of thelight source 501 under different detection modules to implement thecalibration for the scatter diagram position. For example, the power ofthe light source 501 under white cell classification detection module isselected optimally as 5 mW, and the laser power under the reticulocytesdetection mode is configured as 15 mW. However, the power increase ofthe light source 501 causes cost climbing correspondingly.

In one embodiment for detecting a sample containing reticulocytes usingthe sample analyzer of this application, under the configuration of areticulocytes detection mode of the sample analyzer, a scatter diagramof reticulocytes is acquired according to side fluorescent strengthinformation and forward diffusion light strength information. Mature redblood cells, reticulocytes, platelets and white blood cells could bedistinguished from the scatter diagram of reticulocytes under abovedisclosed.

In the same way, for another embodiment, it is also workable to detect asample containing nucleated red cells and white blood cells undernucleated red cell mode. Nucleated red cells, white blood cells andbasophile granulocytes are distinguished according to the scatterdiagram of nucleated red cells based on side fluorescent light strengthinformation and forward diffusion light strength information. The resultis shown in FIG. 18.

Detection result could be displayed on the screenshot of the sampleanalyzer or transmitted to a computer for displaying as well. It isdecided based on the detection requirements and the configuration of thesample analyzer.

In another embodiment of this application, a sample analysis method fora sample analyzer is disclosed, which includes:

providing a sample, the sample includes cell particles processed by areagent;

providing an optical measurement device, the optical measurement deviceincludes a fluid chamber, a light source and a light detector includingat least one silicon photomultiplier;

when the sample forms a sample stream and flows through the fluidchamber, the light source illuminates the sample stream flowing throughthe fluid chamber to generate a light signal and the light detectorreceives the light signal and transforms the light signal into anelectrical signal; and

classifying the cell particles according to the electrical signal.

Detection for the sample containing white blood cell, reticulocytes andnuclear red blood cell is selected for instance and described below. Asabove disclosed method, a processed sample is provided to the opticaldetection device. The sample stream flows through the fluid chamber andis illuminated by the light source with 5-15 mW power to generate lightsignal. The silicon photomultiplier in the light detector has severalarrays including multiple light sensing units respectively. The lightsensing area of each light sensing unit is small than the imaging areaof a single cell particle. A reverse bias voltage larger than thebreakdown voltage is applied on the light sensing unit. The lightdetector receives the light signal and transforms the light signal intoan electrical signal. Each electrical signal reflects the strength ofthe optical signal of each cell particle, such as the strength of thefluorescent light. Differences of those electrical signals are utilizedto classify and count the cell particles.

In another embodiment, the reverse bias voltage of the optical detectiondevice could be configured according to different operation modes. Forexample, a first reverse bias voltage is applied on the light sensingunit when the cell particles waiting for detecting are white bloodcells, and a second reverse bias voltage is applied on the light sensingunit when the cell particles waiting for detecting are reticulocytes.The first reverse bias voltage is small than the second reverse biasvoltage so that a better sensitivity is ensured for the detection of thereticulocytes. In addition, different amplifier gains could beconfigured according to different modes.

After clinical performance evaluation, the sample analyzer disclosed inthe embodiments of this application conducts tests for white blood cellclassification count, reticulocytes count, nuclear blood cell count andwarming ability for abnormal sample. The result of above tests isconsistent well with the same tests conducted by the blood cellanalyzer.

Above descriptions is disclosed under the examples of fluorescent lightsdetection. However, the above disclosed optical measurement device isalso workable for detecting other types of faint lights, such as sidediffusion lights or light absorption signal.

In some other embodiments, the sample analyzer is able to includemultiple light sources so that multiple paths of fluorescent lights orfaint lights are formed. The silicon photomultiplier could be applied asa light detector to detect above fluorescent lights or faint lights andcombine above fluorescent lights or faint lights with diffusion lightsto implement detections for different cell particles and featureinformation on particles surface.

In some other embodiments, the sample analyzer is also able to beapplied for other kinds of sample, but not limits for blood sampledetection only.

In some other embodiments, multiple silicon photomultipliers could beintegrated to form a silicon photomultiplier array with sufficient areaand number of light sensing units to satisfy user requirements.

It is understandable for the skilled in the art that all or some of theprocesses disclosed in the embodiments of the present application areable to be implemented by instructing relating hardware through computerprograms. Above programs are able to be stored in a readable storingmedia of computer. Above programs are able to include the implement ofall flow charts for all methods disclosed in above embodiments inexecution. The readable storing media include but not limited to selectfrom below: Hard Disc, Optical Disc, Read-Only Memory (ROM) andRandom-Access Memory (RAM).

Although the present disclosure has been described through specificembodiments, the present disclosure is not limited to the specificembodiments described above. Those of skill in the art should understandthat various modifications, alternatives and variations may be madebased on the present disclosure, which all should be within the scope ofprotection of the present disclosure. Furthermore, “a (an) embodiment”or “another embodiment” mentioned above may represent differentembodiments, or may also be combined completely or partly in oneembodiment.

What is claimed is:
 1. A sample analysis method for a sample analyzer,comprising: providing an analyte comprising cell particles treated witha reagent; providing an optical measurement device comprising a fluidchamber, a light source and a light detector comprising at least onesilicon photomultiplier; adjusting a reverse bias voltage applied on thesilicon photomultiplier by a temperature compensation device accordingto a temperature of the silicon photomultiplier so as to keep anovervoltage constant; when the analyte flows through the fluid chamberand forms a sample stream, illuminating the sample stream flowingthrough the fluid chamber by the light source to generate a lightsignal, and transforming the light signal into light signal informationafter the light detector receives the light signal; and classifying thecell particles according to the light signal information.
 2. The sampleanalysis method of claim 1, wherein the cell particles are at leastselected from red blood cells, white blood cells and platelets.
 3. Thesample analysis method of claim 2, wherein the red blood cells comprisenucleated red blood cells and reticulocytes.
 4. The sample analysismethod of claim 1, wherein the light source comprises a laser generator,output power of the laser generator is between 1 to 20 mW.
 5. The sampleanalysis method of claim 1, wherein light power of the light source isbetween 5 to 15 mW.
 6. The sample analysis method of claim 1, whereinthe at least one silicon photomultiplier comprises a plurality of lightsensing units arranged in an array configuration, an illumination areaof each light sensing unit is smaller than an imaging area of a singlecell particle, and a size of each light sensing unit is between 10 m to50 km.
 7. The sample analysis method of claim 1, wherein the at leastone silicon photomultiplier comprises a plurality of light sensing unitsarranged as an array configuration, a number of the plurality of lightsensing units is larger than or equal to
 500. 8. The sample analysismethod of claim 1, wherein the at least one silicon photomultipliercomprises a plurality of light sensing units arranged as an arrayconfiguration, preferably, a number of the plurality of light sensingunits is larger than or equal to
 1280. 9. The sample analysis method ofclaim 1, wherein a light sensing area of the at least one siliconphotomultiplier is between 1-36 mm2, and the light sensing area is acircle with a diameter between 2 mm to 6 mm.
 10. The sample analysismethod of claim 1, wherein a light sensing area of the at least onesilicon photomultiplier is between 1-36 mm2, and the light sensing areais a square with a length between 1 mm to 6 mm.
 11. The sample analysismethod of claim 1, wherein the optical measurement device furthercomprises: an optical path, configured between the fluid chamber and thelight detector, for converging the light signal to form a facula on alight sensing area of the at least one silicon photomultiplier, and thefacula is between 50% to 78% of the light sensing area.
 12. The sampleanalysis method of claim 1, further comprising: controlling a reversebias voltage applied on the at least one silicon photomultiplier by acontroller to keep an overvoltage between 0 to 5 volt, the overvoltageis a difference between the reverse bias voltage and a breakdown voltageof the at least one silicon photomultiplier.
 13. The sample analysismethod of claim 1, wherein controlling a reverse bias voltage applied onthe at least one silicon photomultiplier by a controller to keep anovervoltage between 0 to 5 volt comprises: adjusting the reverse biasvoltage applied on the at least one silicon photomultiplier according todifferent operation modes to control the overvoltage.
 14. The sampleanalysis method of claim 1, further comprising: controlling atemperature of the at least one silicon photomultiplier at aconfiguration temperature by a temperature control device, theconfiguration temperature is selected between 20° C. to 40° C.
 15. Thesample analysis method of claim 1, wherein a sample analyzer comprises acontroller, the temperature compensation device comprises a temperaturesensor, a temperature detection circuit, an AD converter, a temperaturecompensation module, a DA converter, a voltage adjustment circuit and aregulation power supply with an adjustable output, wherein thetemperature sensor and the temperature detection circuit detect thetemperature of the at least one silicon photomultiplier and generate atemperature signal, the AD converter converts the temperature signalinto a digital signal, the temperature compensation module calculates atarget value of the reverse bias voltage of the at least one siliconphotomultiplier, the controller adjusts a circuit parameter of thevoltage adjustment circuit by controlling the DA converter to cause anoutput voltage of the regulation power supply to reach a target value ofthe reverse bias voltage.
 16. The sample analysis method of claim 1,wherein a first reverse bias voltage is applied on the at least onesilicon photomultiplier when the cell particles are white blood cellsand a second reverse bias voltage is applied on the plurality of lightsensing unit when the cell particles are reticulocytes, the firstreverse bias voltage is smaller than the second reverse bias voltage.17. The sample analysis method of claim 1, wherein a reverse biasvoltage applied on the at least one silicon photomultiplier is largerthan a breakdown voltage.